Biological information measurement system

ABSTRACT

A light emitting unit emits first light and second light having different wavelengths. A photoreception unit outputs first and second signals depending on photoreception intensities of the first and second light transmitted through or reflected by biological tissue. A processing period setting unit extracts a signal cycle corresponding to the cardiac cycle for the first or second signal and sets a processing period in a first part dominantly affected by arterial blood flowing to the tissue or a second part dominantly affected by venous blood flowing from the tissue in the signal cycle. First and second change amount acquisition units obtain first and second change amounts corresponding to the attenuation change amounts of the first and second light from the first and second signals in the processing period. A concentration calculation unit calculates the concentration of light absorbing substance in blood from the first and second change amounts.

CROSS-REFERENCE TO RELATED APPLICATION(S)

This application claims priority to and the benefit under 35 U.S.C. §119(a) of the earlier filing date of Japanese Patent Application No.2015-069911 filed Mar. 30, 2015, the disclosure of which is herebyincorporated by reference, in its entirety, for any purpose.

BACKGROUND

Examples of the present invention relate to a system measuringbiological information.

A pulse photometer is known as an example of an apparatus constitutingsuch a biological information measurement system. A pulse photometer isan apparatus for calculating the concentration of a light absorbingsubstance in blood of a subject. Specifically, light having a pluralityof wavelengths illuminates the biological tissue of the subject. Theplurality of wavelengths are determined so that the ratio of theabsorption coefficients of blood differs depending on the concentrationof the light absorbing substance in blood. The amount of light havingeach wavelength transmitted through or reflected by the biologicaltissue is detected. The light amount of each wavelength depends on thepulsation of the blood of the subject. Accordingly, the time-dependentchange of the light amount of each wavelength caused by the pulsation isobtained as a pulse wave signal. The amplitude of the pulse signal ofeach wavelength corresponds to the attenuation change amount of thewaveform. The concentration of the light absorbing substance in blood iscalculated based on the ratio of the attenuation change amount of eachwaveform (see JP-B-53-026437, for example).

Arterial blood oxygen saturation is known as the concentration of alight absorbing substance in blood. Arterial blood oxygen saturation isthe ratio of oxyhemoglobin to the amount of hemoglobin capable ofcarrying oxygen. That is, oxyhemoglobin is an example of a lightabsorbing substance in blood. Another example of a light absorbingsubstance in blood is a dye as an indicator to be administered to ablood flow to measure the transit time of the biological tissue.

SUMMARY

An object of the invention is to easily measure various types ofbiological information using the principle of a pulse photometer.

To achieve the above object, according to a first aspect of theinvention, there is provided a biological information measurement systemincluding a light emitting unit emitting first light having a firstwavelength and second light having a second wavelength, a photoreceptionunit outputting a first signal and a second signal depending onphotoreception intensity of the first light and photoreception intensityof the second light transmitted through or reflected by biologicaltissue of a subject, a processing period setting unit extracting asignal cycle corresponding to a cardiac cycle of the subject for one ofthe first signal and the second signal and setting a processing periodin one of a first part in which an effect of arterial blood flowing tothe biological tissue is dominant and a second part in which an effectof venous blood flowing from the biological tissue is dominant in thesignal cycle, a first change amount acquisition unit acquiring a firstchange amount corresponding to an attenuation change amount of the firstlight based on the first signal in the processing period, a secondchange amount acquisition unit acquiring a second change amountcorresponding to an attenuation change amount of the second light basedon the second signal in the processing period, a concentrationcalculation unit calculating a concentration of a light absorbingsubstance in blood of the subject based on the first change amount andthe second change amount, and an output unit outputting theconcentration.

Examples of the light absorbing substance in blood are oxyhemoglobin,deoxyhemoglobin, a dye, and the like.

In such a structure, the signal cycle corresponding to the cardiac cycleof the subject obtained based on the signal corresponding to thephotoreception intensity in the photoreception unit is divided into thepart in which the effect of arterial blood flowing to the biologicaltissue is dominant and the part in which the effect of venous bloodflowing from the biological tissue is dominant. The processing period isset in only one of these parts and the attenuation change amounts ofthese pieces of light having the individual wavelengths are obtained.The processing period is necessarily shorter than the diastole phase orthe systole phase of the heart of the subject. That is, theconcentration of a light absorbing substance in blood of the subject canbe calculated at high speed while suppressing calculation loads.Accordingly, biological information can be measured easily using theprinciple of a pulse photometer.

The biological information measurement system according to the firstaspect may further include a differential signal acquisition unitacquiring a differential signal by differentiating the one of the firstsignal and the second signal, in which the processing period settingunit sets the processing period in the first part based on a minimumvalue of the differential signal.

In such a structure, only by performing simple processing thatdifferentiates the first signal or the second signal, the processingperiod can be set at the feature point at which the effect arterialblood flowing to the biological tissue is the most dominant.Accordingly, it is possible to improve the effect of the above structurethat can easily measure biological information using the principle ofthe pulse photometer.

Alternatively, the biological information measurement system accordingto the first aspect may further include a differential signalacquisition unit acquiring a differential signal by differentiating theone of the first signal and the second signal, in which the processingperiod setting unit sets the processing period in the second part basedon a maximum value of the differential signal.

In such a structure, only by performing simple processing thatdifferentiates the first signal or the second signal, the processingperiod can be set at the feature point at which the effect of venousblood flowing from the biological tissue is the most dominant.Accordingly, it is possible to improve the effect of the above structurethat can easily measure biological information using the principle ofthe pulse photometer.

To achieve the above object, according to a second aspect of theinvention, there is provided a biological information measurement systemincluding a light emitting unit emitting first light having a firstwavelength and second light having a second wavelength, a photoreceptionunit outputting a first signal or a second signal depending onphotoreception intensity of the first light and photoreception intensityof the second light transmitted through or reflected by biologicaltissue of a subject, a processing period setting unit extracting asignal cycle corresponding to a cardiac cycle of the subject for each ofthe first signal and the second signal and setting a first processingperiod in a first part in which an effect of arterial blood flowing tothe biological tissue and setting a second processing period in a secondpart in which an effect of venous blood flowing from the biologicaltissue is dominant in the signal cycle, a first change amountacquisition unit acquiring a first change amount corresponding to anattenuation change amount of the first light in the first processingperiod based on the first signal in the first processing period, asecond change amount acquisition unit acquiring a second change amountcorresponding to an attenuation change amount of the second light in thefirst processing period based on the second signal in the firstprocessing period, a first concentration calculation unit calculating afirst concentration corresponding to a concentration of a lightabsorbing substance in blood of the subject in the first processingperiod based on the first change amount and the second change amount, athird change amount acquisition unit acquiring a third change amountcorresponding to an attenuation change amount of the first light in thesecond processing period based on the first signal in the secondprocessing period, a fourth change amount acquisition unit acquiring afourth change amount corresponding to an attenuation change amount ofthe second light in the second processing period based on the secondsignal in the second processing period, a second concentrationcalculation unit calculating a second concentration corresponding to theconcentration of the light absorbing substance in blood of the subjectin the second processing period based on the third change amount and thefourth change amount, a transit time calculation unit calculating atransit time of blood in the biological tissue based on the firstconcentration and the second concentration, and, an output unitoutputting at least one of the first concentration, the secondconcentration, and the transit time.

According to the second aspect of the invention as described above,there is provided a biological information measurement system includinga light emitting unit emitting first light having a first wavelength andsecond light having a second wavelength, a photoreception unitoutputting a first signal or a second signal depending on photoreceptionintensity of the first light and photoreception intensity of the secondlight transmitted through or reflected by biological tissue of asubject, a processing period setting unit extracting a signal cyclecorresponding to a cardiac cycle of the subject for each of the firstsignal and the second signal and setting a first processing period in afirst part in which an effect of arterial blood flowing to thebiological tissue and setting a second processing period in a secondpart in which an effect of venous blood flowing from the biologicaltissue is dominant in the signal cycle, a first change amountacquisition unit acquiring a first change amount corresponding to anattenuation change amount of the first light in the first processingperiod based on the first signal in the first processing period, asecond change amount acquisition unit acquiring a second change amountcorresponding to an attenuation change amount of the second light in thefirst processing period based on the second signal in the firstprocessing period, a first concentration calculation unit calculating afirst concentration corresponding to a concentration of a lightabsorbing substance in blood of the subject in the first processingperiod based on the first change amount and the second change amount, athird change amount acquisition unit acquiring a third change amountcorresponding to an attenuation change amount of the first light in thesecond processing period based on the first signal in the secondprocessing period, a fourth change amount acquisition unit acquiring afourth change amount corresponding to an attenuation change amount ofthe second light in the second processing period based on the secondsignal in the second processing period, a second concentrationcalculation unit calculating a second concentration corresponding to theconcentration of the light absorbing substance in blood of the subjectin the second processing period based on the third change amount and thefourth change amount, a transit time calculation unit calculating atransit time of blood in the biological tissue based on the firstconcentration and the second concentration, and, an output unitoutputting at least one of the first concentration, the secondconcentration, and the transit time.

Examples of the light absorbing substance in blood are oxyhemoglobin,deoxyhemoglobin, a dye, and the like.

In such a structure, the signal cycle corresponding to the cardiac cycleof the subject obtained based on the signal corresponding to thephotoreception intensity in the photoreception unit is divided into aportion in which the effect of arterial blood flowing to the biologicaltissue is dominant and a portion in which the effect of venous bloodflowing from the biological tissue is dominant. Then, the attenuationchange amount of these pieces of light having the individual wavelengthsare obtained for both parts, so that two types of concentrations of alight absorbing substance in blood having different time-dependentchange characteristics are obtained. This enables the calculation of thetransit time of blood in the biological tissue while using the principleof a pulse photometer having no invasion. The first processing periodand the second processing period are necessarily shorter than thediastole phase or systole phase of the heart of the subject. That is,the concentration of the light absorbing substance in blood and thetransit time of blood of the subject can be calculated at high speedwhile suppressing calculation loads. Accordingly, biological informationcan be measured easily using the principle of a pulse photometer.

The biological information measurement system according to the secondaspect may be configured such that the transit time calculation unitcalculates the transit time based on a time difference between a timewhen the first concentration takes the maximum value and a time when thesecond concentration takes the maximum value.

Alternatively, the biological information measurement system accordingto the second aspect may be configured such that the transit timecalculation unit calculates the transit time based on a time differencebetween a time when the first concentration exceeds a threshold and atime when the second concentration exceeds the threshold.

Alternatively, the biological information measurement system accordingto the second aspect may be configured such that the transit timecalculation unit calculates the transit time based on a differencebetween a first mean transit time obtained based on time-dependentchange of the first concentration and a second mean transit timeobtained based on time-dependent change of the second concentration.

Alternatively, the biological information measurement system accordingto the second aspect may be configured such that the transit timecalculation unit calculates the transit time based on a crosscorrelation function between the first concentration and the secondconcentration.

The biological information measurement system according to the secondaspect may further include an air circuit supplying air to be inhaled bythe subject and an oxygen concentration adjusting unit adjusting aconcentration of oxygen included in the air.

In such a structure, the arterial blood oxygen saturation of bloodtransmitted through the biological tissue can be changed by changing theconcentration of oxygen included in air to be inhaled by the subject.That is, it is possible to measure the transit time of blood in thebiological tissue of the subject using the principle of a pulsephotometer without the need to administer an indicator to a blood flow.Accordingly, biological information of the subject can be measured moreeasily using the principle of a pulse photometer.

The biological information measurement system according to the secondaspect may further include a cuff attachable to the subject so as topress a part of a blood flow upstream of the biological tissue and apressure control unit capable of controlling pressure of the cuff.

In such a structure, the arterial blood oxygen saturation of blood canbe changed by stopping a blood flow through pressing with the cuff. Thatis, it is possible to measure the transit time of blood in thebiological tissue of the subject using the principle of a pulsephotometer without the need to administer an indicator to a blood flow.Accordingly, biological information of the subject can be measured moreeasily using the principle of a pulse photometer.

The biological information measurement system according to the secondaspect may further include a notifying unit making a notice when a valueof the transit time falls outside a predetermined range.

In such a structure, the notice from the notifying unit helps todetermine peripheral circulation incompetence. For example, when thevalue of the transit time falls below a predetermined range, the diseasestate of sepsis can be suspected.

To achieve the above object, according to a third aspect of theinvention, there is provided a light emitting unit emitting first lighthaving a first wavelength and second light having a second wavelength, aphotoreception unit outputting a first signal and a second signaldepending on photoreception intensity of the first light andphotoreception intensity of the second light transmitted through orreflected by biological tissue of a subject, a correlation coefficientacquisition unit acquiring a correlation coefficient between the firstsignal and the second signal, a transit time calculation unitcalculating a transit time of blood in the biological tissue based ontime-dependent change of the correlation coefficient, and an output unitoutputting the concentration.

In such a structure, it is possible to measure the transit time of bloodin the biological tissue of the subject using the principle of a pulsephotometer without the need to administer an indicator to a blood flow.In addition, the transit time can be calculated using simple processingthat acquires the correlation coefficient between the first signal andthe second signal. Accordingly, biological information of the subjectcan be measured more easily using the principle of a pulse photometer.

The biological information measurement system according to the thirdaspect may further include a notifying unit making a notice when a valueof the transit time falls outside a predetermined range.

In such a structure, the notice from the notifying unit helps todetermine peripheral circulation incompetence. For example, when thevalue of the transit time falls below a predetermined range, the diseasestate of sepsis can be suspected.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a block diagram illustrating a structure of a biologicalinformation measurement system according to a first embodiment.

FIGS. 2A-B illustrate a process performed by the biological informationmeasurement system in FIG. 1.

FIG. 3 is a block diagram illustrating a structure of a biologicalinformation measurement system according to a second embodiment.

FIGS. 4A-B illustrate a process performed by the biological informationmeasurement system in FIG. 3.

FIGS. 5A-C illustrate a process performed by the biological informationmeasurement system in FIG. 3.

FIGS. 6A-B illustrate a process performed by the biological informationmeasurement system in FIG. 3.

FIG. 7 is a block diagram illustrating a structure of a biologicalinformation measurement system according to a third embodiment.

FIGS. 8A-G illustrate a process performed by the biological informationmeasurement system in FIG. 7.

FIGS. 9A-C illustrate a process performed by the biological informationmeasurement system in FIG. 7.

DETAILED DESCRIPTION

Examples of embodiments will be described in detail below with referenceto the attached drawings.

FIG. 1 is a block diagram illustrating a functional structure of abiological information measurement system 1 (abbreviated below as themeasurement system 1) according to a first embodiment.

The measurement system 1 includes a light emitting unit 10. The lightemitting unit 10 is configured to emit first light having a firstwavelength λ1 and second light having a second wavelength λ2. The firstwavelength λ1 is 880 nm or 940 nm, for example. The second wavelength λ2is 660 nm or 805 nm, for example. The first light is emitted from, forexample, a semiconductor light emitting device. The second light isemitted from, for example, a semiconductor light emitting device.Examples of the semiconductor light emitting device are a light emittingdiode (LED), laser diode, organic EL device, and the like.

The first wavelength λ1 and second wavelength λ2 are determined asappropriate depending on the type of light absorbing substance in bloodfor which the concentration is calculated. Examples of the lightabsorbing substance in blood are oxyhemoglobin, a dye (for example,indocyanine green) to be administered to a blood flow, and the like.Specifically, the wavelengths are determined so that the ratio ofabsorption coefficients of blood substantially differs depending on theconcentration of the light absorber in blood.

The measurement system 1 includes a photoreception unit 20. Thephotoreception unit 20 is configured to output a first signal S1depending on intensity I1 of the first light that has passed through orthat is reflected by a biological tissue 2 of the subject. In addition,the photoreception unit 20 is configured to output a second signal S2depending on intensity I2 of the second light that has passed through orthat is reflected by the biological tissue 2 of the subject. Thephotoreception unit 20 is, for example, an optical sensor sensitive tothe first wavelength λ1 and the second wavelength λ2. Examples of theoptical sensor are a photodiode, phototransistor, photoresistor, and thelike.

The measurement system 1 includes a processing period setting unit 30.The processing period setting unit 30 is configured to extract a signalcycle corresponding to the cardiac cycle of the subject for one of thefirst signal S1 and the second signal S2 and set the processing periodin one of the first part in which the effect of arterial blood flowingto the biological tissue 2 is dominant and the second part in which theeffect of venous blood flowing from the biological tissue 2 is dominant.

A case in which the above processing is performed for the first signalS1 will be described with reference to FIG. 2A. A waveform illustratedin FIG. 2A corresponds to time-dependent changes of the intensity of thefirst signal S1. As described above, the intensity of the first signalS1 corresponds to the intensity I1 of the first light in thephotoreception unit 20. Accordingly, a horizontal axis in FIG. 2Arepresents time. A vertical axis represents a logarithmic value of theintensity I1 of the first light. The processing period setting unit 30is configured to obtain the intensity of the first signal S1 atpredetermined sampling periods. Each of a plurality of small circlesindicated along the waveform represents the intensity of the firstsignal S1 obtained at each sampling point.

In FIG. 2A, a local maximal value of the logarithmic value is indicatedas I_(dia) and a local minimal value of the logarithmic value isindicated as I_(sys). A time when the above logarithmic value becomesthe local maximal value I_(dia) is indicated as t_(dia). A time when theabove logarithmic value becomes the local minimal value I_(sys) isindicated as t_(sys). The processing period setting unit 30 isconfigured to treat the time period from the time t_(dia) to the timet_(dia) or the time period from the time t_(sys) to the time t_(sys) asthe signal cycle corresponding to the cardiac cycle of the subject.

In the signal cycle, in a period T1 (an example of a first period) fromthe time t_(dia) to the time t_(sys) during which the intensity I1 ofthe first light reduces, the effect of arterial blood flowing to thebiological tissue 2 is dominant. In addition, in a period T2 (an exampleof the second period) from the time t_(sys) to the time t_(dia) duringwhich the intensity I1 of the first light increases, venous bloodflowing from the biological tissue 2 is dominant. The processing periodsetting unit 30 is configured to set the processing period for acquiringthe attenuation change amount, which will be described later, for one ofthe period T1 and the period T2. The processing period is determined tobe shorter than the period T1 and the period T2 and is furtherdetermined to be at least one sampling period. In FIG. 2A, a processingperiod for the period T1 is shown as t_(in). A processing period for theperiod T2 is shown as t_(out).

Although not illustrated, the processing period setting unit 30 isconfigured to be able to perform the same processing for the secondsignal S2. The signal to be processed is determined as appropriatedepending on the type of a light absorbing substance in blood for whichthe concentration is calculated.

The measurement system 1 includes a first change amount acquisition unit41. The first change amount acquisition unit 41 is configured to obtaina first change amount ΔA1 corresponding to the attenuation change amountof the first light based on the first signal S1 (T) in the processingperiod set by the processing period setting unit 30.

When the processing period set by the processing period setting unit 30is t_(in) in the first period T1, the first change amount ΔA1 isobtained by the following expression.

$\begin{matrix}{{\Delta\; A\; 2} = {\log\left\lbrack {I\; 2{\left( {t\; 1} \right)/I}\; 2\left( {t\; 2} \right)} \right\rbrack}} \\{= {{\log\left\lbrack {I\; 2\left( {t\; 1} \right)} \right\rbrack} - {\log\left\lbrack {I\; 2\left( {t\; 2} \right)} \right\rbrack}}}\end{matrix}$

In this expression, t1 represents the starting point of the processingperiod t_(in) and t2 represents the end point of the processing periodt_(in).

When the processing period set by the processing period setting unit 30is t_(out) in the second period T2, the first change amount ΔA1 isobtained by the following expression.

$\begin{matrix}{{\Delta\; A\; 2} = {\log\left\lbrack {I\; 2{\left( {t\; 4} \right)/I}\; 2\left( {t\; 3} \right)} \right\rbrack}} \\{= {{\log\left\lbrack {I\; 2\left( {t\; 3} \right)} \right\rbrack} - {\log\left\lbrack {I\; 2\left( {t\; 3} \right)} \right\rbrack}}}\end{matrix}$

In this expression, t3 represents the starting point of the processingperiod t_(out) and t4 represents the end point of the processing periodt_(out).

The measurement system 1 includes a second change amount acquisitionunit 42. The second change amount acquisition unit 42 is configured toobtain the second change amount ΔA2 corresponding to the attenuationchange amount of the second light based on the second signal S2(T) inthe processing period set by the processing period setting unit 30.

When the processing period set by the processing period setting unit 30is t_(in) in the first period T1, the second change amount ΔA2 isobtained by the following expression.

$\begin{matrix}{{\Delta\; A\; 1} = {\log\left\lbrack {I\; 1{\left( {t\; 1} \right)/I}\; 1\left( {t\; 2} \right)} \right\rbrack}} \\{= {{\log\left\lbrack {I\; 1\left( {t\; 1} \right)} \right\rbrack} - {\log\left\lbrack {I\; 1\left( {t\; 2} \right)} \right\rbrack}}}\end{matrix}$

In this expression, t1 represents the starting point of the processingperiod t_(in) and t2 represents the end point of the processing periodt_(in).

When the processing period set by the processing period setting unit 30is t_(out) in the second period T2, the second change amount ΔA2 isobtained by the following expression.

$\begin{matrix}{{\Delta\; A\; 1} = {\log\left\lbrack {I\; 1{\left( {t\; 4} \right)/I}\; 1\left( {t\; 3} \right)} \right\rbrack}} \\{= {{\log\left\lbrack {I\; 1\left( {t\; 4} \right)} \right\rbrack} - {\log\left\lbrack {I\; 1\left( {t\; 3} \right)} \right\rbrack}}}\end{matrix}$

In this expression, t3 represents the starting point of the processingperiod t_(out) and t4 represents the end point of the processing periodt_(out).

The measurement system 1 includes a concentration calculation unit 50.The concentration calculation unit 50 is configured to calculate aconcentration C of a light absorbing substance in blood of the subjectbased on the first change amount ΔA1 obtained by the first change amountacquisition unit 41 and the second change amount ΔA2 obtained by thesecond change amount acquisition unit 42. Specifically, theconcentration calculation unit 50 is configured to calculate a changeamount ratio Φ, which is the ratio of the second change amount ΔA2 tothe first change amount ΔA1. The concentration C of the light absorbingsubstance in blood is given by the following expression as a function ofthe change amount ratio Φ. The function f depends on the light absorbingsubstance in blood.C=f(Φ)

When the arterial blood oxygen saturation is calculated as theconcentration of a light absorbing substance in blood, the ratio ofoxyhemoglobin to the amount of hemoglobin capable of carrying oxygen isobtained. As this ratio increases, the ratio of deoxyhemoglobin reduces.That is, when the arterial blood oxygen saturation is calculated, theratio of deoxyhemoglobin is treated as the concentration of a lightabsorbing substance in blood.

The measurement system 1 includes an output unit 60. The output unit 60is configured to output the concentration C calculated by theconcentration calculation unit 50. The output unit 60 may have variousaspects. For example, the output unit 60 may be a display unit visuallyproviding the concentration C. Alternatively, the output unit 60 may beconfigured to providing the concentration C as a voice output.Alternatively, the output unit 60 may be configured as a terminalcapable of outputting a signal indicating the concentration Cexternally.

In the embodiment, the signal cycles corresponding to the cardiac cyclesof the subject obtained based on the signal corresponding to thephotoreception intensity in the photoreception unit 20 is divided into aportion in which the effect of arterial blood flowing to the biologicaltissue 2 is dominant and a portion in which the effect of venous bloodflowing from the biological tissue 2 is dominant. The processing periodis set for only one of both portions and the attenuation change amountof each light having each individual wavelength is obtained. Theprocessing period is necessarily shorter than the diastole phase or thesystole phase of the heart of the subject. That is, the concentration ofa light absorbing substance in blood of the subject can be calculated athigh speed while suppressing calculation loads. Accordingly, biologicalinformation can be measured easily using the principle of a pulsephotometer.

As illustrated by dashed lines in FIG. 1, the measurement system 1 mayinclude a differential signal acquisition unit 31. The differentialsignal acquisition unit 31 is configured to obtain a differential signalby differentiating one of the first signal S1 and the second signal S2for which the processing period setting unit 30 sets the processingperiod. In FIG. 1, the differential signal of the first signal S1 isindicated as DS1 and the differential signal of the first signal S2 isindicated as DS2.

A case in which a differential signal DS1 is obtained from the firstsignal S1 will be described with reference to FIG. 2B. A waveformillustrated in FIG. 2B corresponds to the time-dependent change of theintensity of the differential signal DS1. As described above, theintensity of the differential signal DS1 corresponds to thedifferentiated value of the intensity I1 of the first light.Accordingly, a horizontal axis represents time in FIG. 2B. A verticalaxis indicates the differentiated value of the logarithmic value of theintensity I1 of the first light.

In FIG. 2B, a maximum value of the differentiated value is indicated asDI_(dia) and a minimum value of the differentiated value is indicated asDI_(sys). The differentiated value corresponds to the change in theamount (that is, the amount of blood flow) of blood through which thefirst light passes. Accordingly, the minimum value DI_(sys) of thedifferentiated value indicates the point at which the ratio of theinflow amount of arterial blood to the outflow amount of venous bloodbecomes maximum. The maximum value DI_(dia) of the differentiated valueindicates the point at which the ratio of the outflow amount of venousblood to the inflow amount of arterial blood becomes maximum.

In this case, the processing period setting unit 30 is configured to setthe processing period t_(in) in the first period T1 of the cardiac cyclebased on the minimum value of the differential signal DS1 correspondingto the minimum value DI_(sys) of the differentiated value. For example,the processing period t_(in) is determined to be shorter than the periodT1 and to be at least one sampling period of the first signal S1beginning with the time corresponding to the minimum value of thedifferential signal DS1.

In such a structure, only by performing simple processing thatdifferentiates the first signal S1, the processing period t_(in) can beset at the feature point at which the effect of arterial blood flowingto the biological tissue 2 is the most dominant. Accordingly, it ispossible to improve the effect of the above structure that can easilymeasure biological information using the principle of the pulsephotometer.

Alternatively, the processing period setting unit 30 is configured toset the processing period t_(out) in the second period T2 of the cardiaccycle based on the maximum value of the differential signal DS1corresponding to the maximum value DI_(dia) of the differentiated value.For example, processing period t_(out) is determined to be shorter thanthe period T2 and to be at least one sampling period of the first signalS1 beginning with the time corresponding to the maximum value of thedifferential signal DS1.

In such a structure, only by performing simple processing thatdifferentiates the first signal S1, the processing period t_(out) can beset at the feature point at which the effect of venous blood flowingfrom the biological tissue 2 is the most dominant. Accordingly, it ispossible to improve the effect of the above structure that can easilymeasure biological information using the principle of the pulsephotometer.

Although not illustrated, the differential signal acquisition unit 31 isconfigured to be able to perform the same processing for the secondsignal S2. The signal to be processed is determined as appropriatedepending on the type of a light absorbing substance in blood for whichthe concentration is calculated.

In the measurement system 1, the functions of the processing periodsetting unit 30, the differential signal acquisition unit 31, the firstchange amount acquisition unit 41, the second change amount acquisitionunit 42, and the concentration calculation unit 50 are provided bysoftware executed by a combination of a processor and a memoryinterconnected communicably. Examples of the processor include a centralprocessing unit (CPU) and a microprocessor unit (MPU). Examples of thememory include a random access memory (RAM) and read-only memory (ROM).However, at least one of the functions of the processing period settingunit 30, the differential signal acquisition unit 31, the first changeamount acquisition unit 41, the second change amount acquisition unit42, and the concentration calculation unit 50 may be provided byhardware such as circuit devices or a combination of hardware andsoftware.

FIG. 3 is a block diagram illustrating the functional structure of abiological information measurement system 101 (abbreviated hereinafteras the measurement system 101) according to a second embodiment.Components having the same structures or functions as in the measurementsystem 1 according to the first embodiment are given the same referencenumerals and duplicate descriptions are omitted.

The measurement system 101 includes a processing period setting unit130. The processing period setting unit 130 is configured to extract thesignal cycle corresponding to the cardiac cycle of the subject for eachof the first signal S1 and the second signal S2. The case in which theabove processing is performed for the first signal S1 will be describedwith reference to FIG. 4A. Since FIG. 4A is identical to FIG. 2A,duplicate descriptions are omitted. The processing period setting unit130 is configured to be able to perform the same processing for thesecond signal S2.

The processing period setting unit 130 is configured to assume the timeperiod from the time t_(dia) to the time t_(dia) or the time period fromthe time t_(sys) to the time t_(sys) as the signal cycle correspondingto the cardiac cycle of the subject. The processing period setting unit130 is configured to set the first processing period t_(in) in the firstperiod T1 in which arterial blood flowing to the biological tissue 2 isdominant and set the second processing period t_(out) in the secondperiod T2 in which venous blood flowing from the biological tissue 2 isdominant. The processing period is determined to be shorter than theperiod T1 and the period T2 and to be at least one sampling period.

In the setting of the first processing period and the second processingperiod, it is possible to apply the structure and function of thedifferential signal acquisition unit 31 described with reference to themeasurement system 1 according to the first embodiment.

The measurement system 101 includes a first change amount acquisitionunit 141. The first change amount acquisition unit 141 is configured toobtain the first change amount ΔA1 corresponding to the attenuationchange amount of the first light in the first processing period t_(in)set by the processing period setting unit 130 based on the first signalS1 (T1) in the first processing period t_(in). The first change amountΔA1 is obtained by the following expression.

$\begin{matrix}{{\Delta\; A\; 1} = {\log\left\lbrack {I\; 1{\left( {t\; 1} \right)/I}\; 1\left( {t\; 2} \right)} \right\rbrack}} \\{= {{\log\left\lbrack {I\; 1\left( {t\; 1} \right)} \right\rbrack} - {\log\left\lbrack {I\; 1\left( {t\; 2} \right)} \right\rbrack}}}\end{matrix}$

In this expression, t1 represents the starting point of the firstprocessing period t_(in) and t2 represents the end point of the firstprocessing period t_(in).

The measurement system 101 includes a second change amount acquisitionunit 142. The second change amount acquisition unit 142 is configured toobtain the second change amount ΔA2 corresponding to the attenuationchange amount of the second light in the first processing period t_(in)set by the processing period setting unit 130 based on the second signalS2 (T1) in the first processing period t_(in). The second change amountΔA2 is obtained by the following expression.

$\begin{matrix}{{\Delta\; A\; 2} = {\log\left\lbrack {I\; 2{\left( {t\; 1} \right)/I}\; 2\left( {t\; 2} \right)} \right\rbrack}} \\{= {{\log\left\lbrack {I\; 2\left( {t\; 1} \right)} \right\rbrack} - {\log\left\lbrack {I\; 2\left( {t\; 2} \right)} \right\rbrack}}}\end{matrix}$

In this expression, t1 represents the starting point of the processingperiod t_(in) and t2 represents the end point of the first processingperiod t_(in).

The measurement system 101 includes a third change amount acquisitionunit 143. The third change amount acquisition unit 143 is configured toobtain a third change amount ΔA3 corresponding to the attenuation changeamount of the first light in the second processing period t_(out) set bythe processing period setting unit 130 based on the first signal S1 (T2)in the second processing period t_(out). The third change amount ΔA3 isobtained by the following expression.

$\begin{matrix}{{\Delta\; A\; 3} = {\log\left\lbrack {I\; 1{\left( {t\; 4} \right)/I}\; 1\left( {t\; 3} \right)} \right\rbrack}} \\{= {{\log\left\lbrack {I\; 1\left( {t\; 4} \right)} \right\rbrack} - {\log\left\lbrack {I\; 1\left( {t\; 3} \right)} \right\rbrack}}}\end{matrix}$

In this expression, t3 represents the starting point of the secondprocessing period t_(out) and t4 represents the end point of the secondprocessing period t_(out).

The measurement system 101 includes a fourth change amount acquisitionunit 144. The fourth change amount acquisition unit 144 is configured toobtain a fourth change amount ΔA4 corresponding to the attenuationchange amount of the second light in the second processing periodt_(out) set by the processing period setting unit 130 based on thesecond signal S2 (T2) in the second processing period t_(out). Thefourth change amount ΔA4 is obtained by the following expression.

$\begin{matrix}{{\Delta\; A\; 4} = {\log\left\lbrack {I\; 2{\left( {t\; 4} \right)/I}\; 2\left( {t\; 3} \right)} \right\rbrack}} \\{= {{\log\left\lbrack {I\; 2\left( {t\; 3} \right)} \right\rbrack} - {\log\left\lbrack {I\; 2\left( {t\; 3} \right)} \right\rbrack}}}\end{matrix}$

In this expression, t3 represents the starting point of the processingperiod t_(out) and t4 represents the end point of the processing periodt_(out).

The measurement system 101 includes a first concentration calculationunit 151. The first concentration calculation unit 151 is configured toobtain the first concentration C1 corresponding to the concentration ofa light absorbing substance in blood of the subject in the first thefirst processing period t_(in) based on the first change amount ΔA1obtained by the first change amount acquisition unit 141 and the secondchange amount ΔA2 obtained by the second change amount acquisition unit142. Specifically, the first concentration calculation unit 151 isconfigured to calculate a first change amount ratio Φ_(in), which is theratio of the second change amount ΔA2 to the first change amount ΔA1.The first concentration C1 is given by the following expression as afunction of the first change amount ratio Φ_(in). The function f1depends on the light absorbing substance in blood.C1=f1(Φ_(in))

The measurement system 101 includes a second concentration calculationunit 152. The second concentration calculation unit 152 is configured tocalculate a second concentration C2 corresponding to the concentrationof a light absorbing substance in blood of the subject in the secondprocessing period t_(out) based on the third change amount ΔA3 obtainedby the third change amount acquisition unit 143 and the fourth changeamount ΔA4 obtained by the fourth change amount acquisition unit 144.Specifically, the second concentration calculation unit 152 isconfigured to calculate a second change amount ratio Φ_(out), which isthe ratio of the fourth change amount ΔA4 to the third change amountΔA3. The second concentration C2 is given by the following expression asa function of the second change amount ratio Φ_(out). The function f2depends on the light absorbing substance in blood.C2=f2(Φ_(out))

The measurement system 101 includes a transit time calculation unit 153.The transit time calculation unit 153 is configured to calculate atransit time Tt of blood in the biological tissue 2 based on the firstconcentration C1 calculated by the first concentration calculation unit151 and the second concentration C2 calculated by the secondconcentration calculation unit 152.

FIG. 4B illustrates the operation of the transit time calculation unit153. FIG. 4B illustrates the time-dependent change of the first changeamount ratio Φ_(in) corresponding to the first concentration C1 and thesecond change amount ratio Φ_(out) corresponding to the secondconcentration C2. Circles FIG. 4B indicate the time-dependent change ofthe attenuation change amount obtained by a conventional pulsephotometer as a comparison example. In the conventional pulsephotometer, between the time (that is, t_(dia)) when the photoreceptionintensity in the photoreception unit becomes the maximum and the time(that is, t_(sys)) when the photoreception intensity becomes theminimum, the attenuation is obtained for each of light having eachwavelength and the attenuation ratio is calculated. Here, 940 nm isselected as the first wavelength λ1 and 805 nm is selected as the secondwavelength λ2. The first change amount ratio Φ_(in) and the secondchange amount ratio Φ_(out) are calculated by the following expressions.Φ_(in) =ΔA2/ΔA1Φ_(out) =ΔA4/ΔA3

The time-dependent change of the first change amount ratio Φ_(in) inwhich the effect of arterial blood flowing to the biological tissue 2 isdominant is similar, in principle, to the time-dependent change of thechange amount ratio calculated by a conventional pulse photometer.However, the time-dependent change of the second change amount ratioΦ_(out) in which the effect of venous blood flowing from the biologicaltissue 2 is dominant is significantly different from the time-dependentchange of the first change amount ratio Φ_(in). Specifically, the secondchange amount ratio Φ_(out) increases monotonically and reducesmonotonically behind the first change amount ratio Φ_(in). This timedelay corresponds to the transit time of blood Tt in the biologicaltissue 2 to be calculated.

The measurement system 101 includes an output unit 160. The output unit160 is configured to output at least one of the first concentration C1calculated by the first concentration calculation unit 151, the secondconcentration C2 calculated by the second concentration calculation unit152, and the transit time Tt calculated by the transit time calculationunit 153. The output unit 160 may have various aspects. For example, theoutput unit 160 may be a display unit visually providing at least one ofthe first concentration C1, the second concentration C2, and the transittime Tt. Alternatively, the output unit 160 may be configured to provideat least one of the first concentration C1, second concentration C2, andthe transit time Tt as a voice output. Alternatively, the output unit160 may be configured as a terminal capable of outputting a signalindicating at least one of the first concentration C1, secondconcentration C2, and the transit time Tt.

Conventionally, an indicator dilution method has been used to measurethe transit time. A dye is often used as an indicator. The dye isadministered upstream of a blood flow to be transferred to thebiological tissue to draw the dye densitogram indicating thetime-dependent change of the concentration of the dye in blood for eachof the blood vessel through which the blood flows to the biologicaltissue and the blood vessel through which the blood flows from thebiological tissue.

When the concentration of the dye is measured at a measurement point Afrom which arterial blood flows to the biological tissue, a dyedensitogram as illustrated in FIG. 5A is acquired. The dye isadministered at time 0. The administered dye is transferred to thebiological tissue while being diffused by a blood flow. The dyedensitogram obtained at the measurement point A has a curve thatincreases monotonically, reduces monotonically, and has a single peak.The time period from the time when the dye is administered and the timewhen the area under the curve (AUC) is halved is referred to as a meantransit time (MTT). In FIG. 5A, the mean transit time at the measurementpoint A is indicated as MTTA.

The dye having been transmitted the biological tissue appears at ameasurement point B at which venous blood flows. When the concentrationof the dye is measured at the measurement point B, a dye densitogram asillustrated in FIG. 5B is obtained. The dye is administered at time 0.The concentration increases monotonically behind the measurement point Aand the peak of the curve is reduced by the amount of diffusion. In FIG.5B, the mean transit time at the measurement point B is indicated asMTTB.

Since the dye does not disappear after being transmitted through thebiological tissue, the area under the curve at the measurement point Ais the same as the area under the curve at the measurement point B. Thetime difference (MTT A to B) between MTTA and MTTB in FIG. 5Ccorresponds to the time for the dye to be transmitted through thebiological tissue, that is, the transit time of blood in the biologicaltissue.

If a catheter is inserted into the measurement point A and themeasurement point B and the concentration of the dye is measured whiledrawing blood continuously (a cuvette method), the transit time of bloodequivalent to the time difference between MTTA and MTTB is obtained.However, invasion with a catheter gives excessive loads to the subject.

The pulse dye dilution method has been known as a non-invasive method.In this method, the concentration of a dye in arterial blood is measuredcontinuously using the principle of a pulse photometer. However, thismethod can obtain only the concentration of the dye in arterial blood.Accordingly, MTTA can be obtained, but the time difference between MTTAand MTTB cannot be obtained. The curve illustrated as a comparisonexample in FIG. 4B corresponds to the dye densitogram obtained by thepulse dye dilution method.

In the embodiment, the signal cycle corresponding to the cardiac cycleof the subject obtained based on the signal corresponding to thephotoreception intensity in the photoreception unit 20 is divided into aportion in which the effect of arterial blood flowing to the biologicaltissue 2 is dominant and a portion in which the effect of venous bloodflowing from the biological tissue 2 is dominant. An attenuation changeamount of each light having each wavelength is obtained for bothportions, so that two types of concentrations of light absorbingsubstance in blood having different time-dependent changecharacteristics are obtained as in the dye densitograms illustrated inFIGS. 5A and 5B. This enables the calculation of the transit time Tt ofblood in the biological tissue 2 while using the principle of a pulsephotometer without invasion.

The first processing period and the second processing period arenecessarily shorter than the diastole phase or the systole phase of theheart of the subject. That is, the concentration of a light absorbingsubstance in blood and the transit time of blood of the subject can becalculated at high speed while suppressing calculation loads.Accordingly, biological information can be measured easily using theprinciple of a pulse photometer.

Some examples can be considered as methods for obtaining the transittime Tt based on the first change amount ratio Φ_(in) corresponding tothe first concentration C1 and the second change amount ratio Φ_(out)corresponding to the second concentration C2 illustrated in FIG. 4B.

In the example illustrated in FIG. 4B, the transit time Tt is calculatedbased on the difference in the mean transit time obtained from thetime-dependent change of the change amount ratios as in the exampleillustrated in FIG. 5C. Specifically, the time period until the areaunder the curve (AUC) is halved is obtained as the second mean transittime from the time-dependent change of the first change amount ratioΦ_(in). Similarly, the time period until the area under the curve (AUC)is halved is obtained as the second mean transit time from thetime-dependent change of the second change amount ratio Φ_(out). Thetransit time Tt is calculated as the difference between the first meantransit time and the second mean transit time.

Alternatively, the transit time Tt may calculated based on the timedifference between the time when the first change amount ratio Φ_(in)becomes the maximum value and the time when the second change amountratio Φ_(out) becomes the maximum value.

Alternatively, the transit time Tt may calculated based on the timedifference between a time when the first change amount ratio Φ_(in)exceeds a predetermined threshold and a time when the second changeamount ratio Φ_(out) exceeds the predetermined threshold. In this case,the threshold needs to be set to a value lower than the maximum value ofthe second change amount ratio Φ_(out), which is lower than the maximumvalue of the first change amount ratio Φ_(in).

Alternatively, the transit time Tt may be calculated based on a crosscorrelation function between the first change amount ratio Φ_(in) andthe second change amount ratio Φ_(out). Since the time-dependent changecharacteristics of the first change amount ratio Φ_(in) are similar tothe time-dependent change characteristics of the second change amountratio Φ_(out), a time period from a reference time related to the firstchange amount ratio Φ_(in) to the time when the maximum value of thecross correlation function is obtained can be assumed to be the delay inthe time-dependent change of the second change amount ratio Φ_(out) fromthe time-dependent change of the first change amount ratio Φ_(in). Thisdelay is calculated as the transit time Tt.

The transit time Tt can be also calculated based on the time-dependentchange of the arterial blood oxygen saturation. Such examples will bedescribed below.

As illustrated by dashed lines in FIG. 3, the measurement system 101 mayinclude an air circuit 111 and an oxygen concentration adjusting unit112. In this case, the air circuit 111 is configured to be able tosupply air to be inhaled by the subject. The oxygen concentrationadjusting unit 112 is configured to adjust an oxygen concentration FiO2included in air to be supplied via the air circuit 111.

The oxygen concentration adjusting unit 112 reduces the oxygenconcentration FiO2 in air to be inhaled by the subject, for apredetermined period. After that, the oxygen concentration adjustingunit 112 returns the oxygen concentration FiO2 to the normal value. FIG.6A illustrates the time-dependent change of the first change amountratio corresponding to the first concentration C1 calculated by thefirst concentration calculation unit 151 and the second change amountratio Φ_(out) corresponding to the second concentration C2 calculated bysecond concentration C2. Here, 940 nm is selected as the firstwavelength λ1 and 660 nm is selected as the second wavelength λ2. Thefirst change amount ratio Φ_(in) and the second change amount ratioΦ_(out) are calculated by the following expression.Φ_(in) =ΔA2/ΔA1Φ_(out) =ΔA4/ΔA3

The first change amount ratio Φ_(in) and the second change amount ratioΦ_(out) have a negative correlation with respect to the arterial bloodoxygen saturation. Accordingly, reduction in the first change amountratio Φ_(in) and the second change amount ratio Φ_(out) indicates anincrease in the arterial blood oxygen saturation. Accordingly, thesechange amount ratios increase as the oxygen concentration FiO2 reducesand these change amount ratios reduce as the concentration of oxygenFiO2 increases. As in the example described above, the time-dependentchange of the first change amount ratio in which the effect of arterialblood flowing to the biological tissue 2 is dominant is similar to thetime-dependent change of the change amount ratio calculated by aconventional pulse photometer. However, the time-dependent change of thesecond change amount ratio Φ_(out) in which the effect of venous bloodflowing from the biological tissue 2 is dominant is significantlydifferent from the time-dependent change of the first change amountratio Φ_(in). Specifically, the second change amount ratio Φ_(out)increases monotonically and reduces monotonically behind the firstchange amount ratio Φ_(in).

In this example, if the value when the first change amount ratio Φ_(in)starts reducing is 100% and the value when the first change amount ratioΦ_(in) ends reducing is 0%, the time difference between the time whenthe first change amount ratio Φ_(in) reduces to the value correspondingto 50% and the time when the second change amount ratio Φ_(out) reducesto the value corresponding to 50% is calculated as the transit time Tt.

Reduction in the oxygen concentration FiO2 by the oxygen concentrationadjusting unit 112 can be considered as pseudo reproduction of the statein which the subject holds the breath. Accordingly, if the subjectawakes, the above change of the arterial blood oxygen saturation canalso be caused by having the subject to hold the breath. In addition,the above change of the arterial blood oxygen saturation can also becaused by having the subject to raise the hand in the state in which thelight emitting unit 10 and the photoreception unit 20 are attached tothe tissue of the fingertip of the subject.

In such a structure, it is possible to measure the transit time Tt ofblood in the biological tissue 2 of the subject using the principle of apulse photometer without the need to administer an indicator to a bloodflow. Accordingly, biological information of the subject can be measuredmore easily using the principle of a pulse photometer. In addition, itis possible to obtain the change history of the transit time Tt byadjusting the concentration of oxygen using the oxygen concentrationadjusting unit 112 at regular time intervals and calculating the transittime Tt. This notifies the trend of the deterioration and improvement inperipheral circulation of the subject.

As illustrated by dashed lines in FIG. 3, the measurement system 101 mayinclude a cuff 113 and a pressure control unit 114. In this case, thecuff 113 can be attached to the subject so as to press a blood flowupstream side of the biological tissue 2 of the subject. For example,when the light emitting unit 10 and the photoreception unit 20 areattached to a tip of a finger, the cuff 113 is attached to a blood flowupstream side of the finger (for example, the part between the secondjoint and the third joint) and the pressure control unit 114 isconfigured to be able to control the pressure of the cuff 113.

The pressure control unit 114 raises the pressure of the cuff 113 byblowing air to the cuff 113. When the pressure of the cuff 113 reaches apredetermined value, the pressure control unit 114 keeps this state fora predetermined time. This presses the part to which the cuff 113 hasbeen attached. After an elapse of the predetermined time, the pressurecontrol unit 114 releases the pressure of the cuff 113. FIG. 6Billustrates the time-dependent change of the first change amount ratioΦ_(in) corresponding to the first concentration C1 calculated by thefirst concentration calculation unit 151 and the second change amountratio Φ_(out) corresponding to the second concentration C2 calculated bythe second concentration calculation unit 152, in this case. For thesame components as in FIG. 6A, duplicate descriptions are omitted.

Since the blood flow stops during pressing, the first signal S1 and thesecond signal S2 having the signal cycle corresponding to the cardiaccycle are not obtained. Accordingly, the first change amount ratioΦ_(in) and the second change amount ratio Φ_(out) are not also obtained.When the pressure of the cuff 113 is released, the first change amountratio Φ_(in) is greatly separated from the second change amount ratioΦ_(out) in the signal cycle corresponding to the first heartbeat. Thisseparation is caused by the difference in the oxygen saturation betweenarterial blood and venous blood. Immediately after release from thepressing, the oxygen saturation of the biological tissue 2 includingvenous blood is low. Venous blood having high oxygen saturation flows inthe biological tissue 2. As blood having small oxygen saturation flowsout, the difference between the first change amount ratio Φ_(in) and thesecond change amount ratio Φ_(out) reduces. The time period from therelease from pressing to a steady state in which the difference betweenboth ratios is substantially zero is calculated as the transit time Tt.The time when the steady state is reached may be, for example, the timewhen the difference between the first change amount ratio Φ_(in) and thesecond change amount ratio Φ_(out) is equal to or less than apredetermined threshold.

Also in such a structure, it is possible to measure the transit time Ttof blood in the biological tissue 2 of the subject using the principleof a pulse photometer without the need to administer an indicator to ablood flow. Accordingly, biological information of the subject can bemeasured more easily using the principle of a pulse photometer. Inaddition, it is possible to obtain the change history of the transittime Tt by adjusting the pressure of the cuff 113 using the pressurecontrol unit 114 at regular time intervals and calculating the transittime Tt. This notifies the trend of the deterioration and improvement inperipheral circulation of the subject.

As illustrated by dashed lines in FIG. 3, the measurement system 101 mayinclude a notifying unit 161. The notifying unit 161 is configured tonotify when the value of the transit time Tt calculated by the transittime calculation unit 153 is outside a predetermined range. Thenotifying unit 161 may have various aspects. For example, the notifyingunit 161 visually notifies the fact that the value of the transit timeTt calculated by the transit time calculation unit 153 is outside thepredetermined range. Alternatively, the notifying unit 161 provides thefact as a voice output. Alternatively, the notifying unit 161 outputs asignal indicating the fact externally.

In such a structure, notification from the notifying unit 161 assistsdiagnosis of peripheral circulation incompetence. For example, when thevalue of the transit time Tt falls below a predetermined range, thedisease state of sepsis may be suspected.

In the disease state of sepsis, the expansion of arteries and arteriols,reduction of peripheral artery resistance, and increase in the amount ofcardiac output first arise. This stage is referred to as a warm shock.Since the blood flows from artery to vein bypassing blood capillary inthis state, oxygen in the peripheral tissue becomes insufficient. Such ablood flow bypassing blood capillary is referred to as a shunt bloodflow. When this disease state progresses, the amount of cardiac outputreduces, the blood pressure reduces, and shock disease occurs. In thisstage, metabolic disorder occurs in the peripheral tissue. Accordingly,it is important to find the disease state in the stage of the warm shockand start treatment in an early stage. Since the blood flow does notpass through the peripheral tissue when a shunt blood flow is present,the difference in the oxygen saturation between artery and vein issmall. Accordingly, the transit time of blood in the peripheral tissuebecomes short. In the above structure, the early detection of thedisease state of sepsis can be helped using simple measurement that usesthe principle of a pulse photometer.

In the measurement system 101, the functions of the processing periodsetting unit 130, the first change amount acquisition unit 141, thesecond change amount acquisition unit 142, the third change amountacquisition unit 143, the fourth change amount acquisition unit 144, thefirst concentration calculation unit 151, the second concentrationcalculation unit 152, and the transit time calculation unit 153 areprovided by software executed by a combination of a processor and amemory interconnected communicably. Examples of the processor are a CPUand MPU. Examples of the memory are a RAM and ROM. However, at least oneof the functions of the processing period setting unit 130, the firstchange amount acquisition unit 141, the second change amount acquisitionunit 142, the third change amount acquisition unit 143, the fourthchange amount acquisition unit 144, the first concentration calculationunit 151, the second concentration calculation unit 152, and the transittime calculation unit 153 may be provided by hardware such as circuitdevices or a combination of hardware and software.

FIG. 7 is a block diagram illustrating the functional structure of abiological information measurement system 201 (abbreviated below as themeasurement system 201) according to a third embodiment. Componentshaving the same structures or functions as in the measurement system 1according to the first embodiment and the measurement system 101according to the second embodiment are given the same reference numeralsand duplicate descriptions are omitted.

The measurement system 201 includes a correlation coefficientacquisition unit 231. The correlation coefficient acquisition unit 231is configured to obtain a correlation coefficient Cc between the firstsignal S1 and the second signal S2 output from the photoreception unit20.

The measurement system 201 includes a transit time calculation unit 253.The transit time calculation unit 253 is configured to calculate thetransit time Tt of blood in the biological tissue 2 based on thecorrelation coefficient Cc obtained by the correlation coefficientacquisition unit 231.

The measurement system 101 according to the second embodiment calculatesthe transit time Tt using the difference in the concentration of a lightabsorbing substance in blood between the blood flowing to the biologicaltissue 2 and the blood flowing from the biological tissue 2. The presentembodiment focuses on the difference between the waveform of the firstsignal S1 in the signal cycle corresponding to the cardiac cycle of thesubject and the waveform of the second signal S2 in the signal cycle andcalculates the transit time Tt based on the difference.

FIG. 8A illustrates the time-dependent change of the logarithmic valueof the intensity I1 of the first light and the logarithmic value of theintensity I2 of the second light when the subject is caused to stop thebreath and then caused to resume the breath after a predetermined time.In this case, 940 nm is selected as the first wavelength λ1 and 660 nmis selected as the second wavelength λ2. Substantially in the middle inthe horizontal direction of FIG. 8A, it can be seen that the directcurrent component of the intensity I2 increases. The increase is causedsince the blood in which the oxygen saturation has been raised byresumption of the breath reaches the biological tissue 2.

FIG. 8B illustrates the time-dependent change of the first change amountratio and the second change amount ratio Φ_(out) measured by themeasurement system 201 according to the second embodiment in this case.

FIG. 8C illustrates the time-dependent change of the correlationcoefficient between the time-dependent change waveform for the intensityI1 and the time-dependent change waveform for the intensity I2illustrated in FIG. 8A. As the comparison in FIG. 8B illustrates, thecorrelation coefficient Cc drops in the period in which the first changeamount ratio Φ_(in) differs from the second change amount ratio Φ_(out).That is, when there is a difference in the oxygen saturation between theblood flowing to the biological tissue 2 and the blood flowing from thebiological tissue 2, the time-dependent change waveform for theintensity I1 is not similar to the time-dependent change waveform forthe intensity I2.

FIG. 8D is an enlarged view of a portion (one signal cycle) indicated bysymbol t_(A) in FIG. 8A. This portion corresponds to the signal cycle inwhich the correlation coefficient Cc is low. FIG. 8E illustrates aLissajous waveform indicating the time-dependent change of thelogarithmic value of the intensity I1 and the logarithmic value of theintensity I2 when the logarithmic value of the intensity I1 is plottedon the horizontal axis and the logarithmic value of the intensity I2 isplotted on the vertical axis.

FIG. 8F is an enlarged view of a portion (one signal cycle) indicated bysymbol t_(B) in FIG. 8A. This portion corresponds to the signal cycle inwhich the correlation coefficient Cc is high. FIG. 8G illustrates aLissajous waveform corresponding to FIG. 8E.

As illustrated in FIG. 8E, when the correlation coefficient Cc is low,the inclinations of the Lissajous figures greatly differ from each otherdue to the difference in the oxygen saturation between the inflow phaseand the outflow phase of a blood flow. As illustrated in FIG. 8G, whenthe correlation coefficient Cc is high, since the difference in theoxygen saturation between the inflow phase and the outflow phase of ablood flow is small, the inclinations of the Lissajous figures do notgreatly differ from each other.

The transit time calculation unit 253 is configured to calculate thetime period from when the correlation coefficient Cc reduces to when thecorrelation coefficient Cc returns to the original value as the transittime Tt. For example, as illustrated in FIG. 8C, a predeterminedthreshold th is set as appropriate. The transit time calculation unit253 may be configured to determine the time period in which thecorrelation coefficient Cc is lower than the threshold th to be thetransit time Tt. The transit time Tt may be determined based on anappropriate rule concerning the Lissajous waveforms illustrated in FIGS.8E and 8G.

The period in which the correlation coefficient acquisition unit 231obtains the correlation coefficient Cc is not limited to one signalcycle corresponding to the cardiac cycle of the subject. The cycle maybe determined arbitrarily as long as the cycle is sufficiently shorter(for example, 1 second) than the transit time.

In this example, the arterial blood oxygen saturation is changed bycausing the subject to stop the breath. However, the arterial bloodoxygen saturation may be changed using a combination of the air circuit111 and the oxygen concentration adjusting unit 112 described withreference to the measurement system 201 according to the secondembodiment or a combination of the cuff 113 and the pressure controlunit 114.

In the structure according to the embodiment, it is possible to measurethe transit time Tt of blood in the biological tissue 2 of the subjectusing the principle of a pulse photometer without the need to administeran indicator to a blood flow. In addition, the transit time Tt can becalculated by simple processing that acquires the correlationcoefficient between the first signal S1 and the second signal S2.Accordingly, biological information of the subject can be measured moreeasily using the principle of a pulse photometer.

FIG. 9A illustrates the time-dependent change of the logarithmic valueof the intensity I1 of the first light and the logarithmic value of theintensity I2 of the second light in the case in which the light emittingunit 10 and the photoreception unit 20 are attached to the fingertip ofthe subject, the subject is made to raise the hand and hold the breath,and made to resume breathing after a predetermined time. In this case,940 nm is selected as the first wavelength λ1 and 660 nm is selected asthe second wavelength λ2. FIG. 9B illustrates the time-dependent changeof the first change amount ratio Φ_(in) and the second change amountratio Φ_(out) measured by the measurement system 201 according to thesecond embodiment in this case.

FIG. 9C illustrates the time-dependent change of the correlationcoefficient between the time-dependent change waveform for the intensityI1 and the time-dependent change waveform for the intensity I2illustrated in FIG. 9A. In this example, as FIG. 9B illustrates, thereis no significant difference between the time-dependent change of thefirst change amount ratio Φ_(in) and the time-dependent change of thesecond change amount ratio Φ_(out). However, if the correlationcoefficient between the time-dependent change waveform for the intensityI1 and the time-dependent change waveform for the intensity I2 isobtained, the difference between the time-dependent change waveform forthe intensity I1 and the time-dependent change waveform for theintensity I2 can be easily recognized. Accordingly, in the structure ofthe present embodiment, even when it is difficult to recognizesignificant difference between the time-dependent change of the firstchange amount ratio Φ_(in) and the time-dependent change of the secondchange amount ratio Φ_(out), the transit time Tt can be calculatedeasily.

In the measurement system 201, the functions of the correlationcoefficient acquisition unit 231 and the transit time calculation unit253 are provided by software executed by a combination of a processorand a memory interconnected communicably. Examples of the processorinclude a CPU and MPU. Examples of the memory include a RAM and ROM.However, at least one of the functions of the correlation coefficientacquisition unit 231 and the transit time calculation unit 253 may beprovided by hardware such as circuit devices or a combination ofhardware and software.

The above embodiments are only examples that facilitate theunderstanding of the invention. The structures according to the aboveembodiments may be changed or modified as appropriate without departingfrom the spirit of the invention. In addition, it will be appreciatedthat equivalents fall within the technical range of the invention.

What is claimed is:
 1. A biological information measurement systemcomprising: a light emitting unit configured to emit first light havinga first wavelength and second light having a second wavelength; aphotoreception unit configured to output a first signal and a secondsignal depending on photoreception intensity of the first light andphotoreception intensity of the second light that has passed throughbiological tissue of a subject or that is reflected by the biologicaltissue of the subject; a processing period setting unit configured toextract a signal cycle corresponding to a cardiac cycle of the subjectfor one of the first signal and the second signal, and furtherconfigured to set a first processing period in one of a first period inwhich an effect of arterial blood flowing to the biological tissue isdominant and a second period in which an effect of venous blood flowingfrom the biological tissue is dominant in the signal cycle; a firstchange amount acquisition unit configured to obtain a first changeamount corresponding to an attenuation change amount of the first lightbased on the first signal in the first processing period; a secondchange amount acquisition unit configured to obtain a second changeamount corresponding to an attenuation change amount of the second lightbased on the second signal in the first processing period; a firstconcentration calculation unit configured to calculate a firstconcentration of a light absorbing substance in blood of the subjectbased on the first change amount and the second change amount; and anoutput unit configured to provide the first concentration.
 2. Thebiological information measurement system according to claim 1, furthercomprising: a differential signal acquisition unit configured to obtaina differential signal by differentiating the one of the first signal andthe second signal, wherein the processing period setting unit isconfigured to set the first processing period in the first period basedon a minimum value of the differential signal.
 3. The biologicalinformation measurement system according to claim 1, further comprising:a differential signal acquisition unit configured to obtain adifferential signal by differentiating the one of the first signal andthe second signal, wherein the processing period setting unit isconfigured to set the first processing period in the second period basedon a maximum value of the differential signal.
 4. The biologicalinformation measurement system according to claim 1, wherein the lightabsorbing substance is oxyhemoglobin or deoxyhemoglobin.
 5. Thebiological information measurement system according to claim 1, whereinthe light absorbing substance is a dye.
 6. The biological informationmeasurement system according to claim 1, wherein the one of the firstsignal and the second signal is the first signal, wherein the one of thefirst period and the second period is the first period, wherein theprocessing period setting unit is further configured to extract thesignal cycle corresponding to the cardiac cycle of the subject for thesecond signal, and further configured to set a second processing periodin the second period, wherein the biological information measurementsystem further comprises: a third change amount acquisition unitconfigured to obtain a third change amount corresponding to anattenuation change amount of the first light in the second processingperiod based on the first signal in the second processing period; afourth change amount acquisition unit configured to obtain a fourthchange amount corresponding to an attenuation change amount of thesecond light in the second processing period based on the second signalin the second processing period; a second concentration calculation unitconfigured to calculate a second concentration corresponding to theconcentration of the light absorbing substance in blood of the subjectin the second processing period based on the third change amount and thefourth change amount; and a transit time calculation unit configured tocalculate a transit time of blood in the biological tissue based on thefirst concentration and the second concentration, and wherein the outputunit is further configured to provide at least one of the firstconcentration, the second concentration, and the transit time.
 7. Thebiological information measurement system according to claim 6, whereinthe transit time calculation unit is configured to calculate the transittime based on a time difference between a time when the firstconcentration becomes the maximum and a time when the secondconcentration becomes the maximum.
 8. The biological informationmeasurement system according to claim 6, wherein the transit timecalculation unit is configured to calculate the transit time based on atime difference between a time when the first concentration exceeds athreshold and a time when the second concentration exceeds thethreshold.
 9. The biological information measurement system according toclaim 6, wherein the transit time calculation unit is configured tocalculate the transit time based on a difference between a first meantransit time acquired based on time-dependent change of the firstconcentration and a second mean transit time acquired based ontime-dependent change of the second concentration.
 10. The biologicalinformation measurement system according to claim 6, wherein the transittime calculation unit is configured to calculate the transit time basedon a cross correlation function between the first concentration and thesecond concentration.
 11. The biological information measurement systemaccording to claim 1, further comprising: an air circuit configured tosupply air to be inhaled by the subject; and an oxygen concentrationadjusting unit configured to adjust a concentration of oxygen includedin the air.
 12. The biological information measurement system accordingto claim 1, further comprising: a cuff attachable to the subjectconfigured to press a blood flow upstream side of the biological tissue.13. The biological information measurement system according to claim 6,further comprising: a notifying unit configured to notify when thetransit time is outside a predetermined range.
 14. A biologicalinformation measurement system comprising: a light emitting unitconfigured to emit first light having a first wavelength and secondlight having a second wavelength; a photoreception unit configured tooutput a first signal and a second signal depending on photoreceptionintensity of the first light and photoreception intensity of the secondlight that has passed through biological tissue of a subject or that isreflected by the biological tissue of the subject; a processing periodset unit configured to extract a signal cycle corresponding to a cardiaccycle of the subject for one of the first signal and the second signal,and further configured to set a first processing period in one of afirst period in which an effect of arterial blood flowing to thebiological tissue is dominant and a second period in which an effect ofvenous blood flowing from the biological tissue is dominant in thesignal cycle; a correlation coefficient acquisition unit configured toobtain a correlation coefficient between the first signal and the secondsignal; a transit time calculation unit configured to calculate atransit time of blood in the biological tissue based on time-dependentchange of the correlation coefficient; and an output unit configured toprovide the transit time.
 15. The biological information measurementsystem according to claim 14, further comprising: a notifying unitconfigured to notify when the transit time is outside a predeterminedrange.
 16. A method of measuring biological information, comprising:emitting first light having a first wavelength and second light having asecond wavelength; outputting a first signal and a second signaldepending on photoreception intensity of the first light andphotoreception intensity of the second light that has passed throughbiological tissue of a subject or that is reflected by the biologicaltissue of the subject; extracting a signal cycle corresponding to acardiac cycle of the subject for one of the first signal and the secondsignal; setting a first processing period in one of a first period inwhich an effect of arterial blood flowing to the biological tissue isdominant and a second period in which an effect of venous blood flowingfrom the biological tissue is dominant in the signal cycle; obtaining afirst change amount corresponding to an attenuation change amount of thefirst light based on the first signal in the first processing period;obtaining a second change amount corresponding to an attenuation changeamount of the second light based on the second signal in the firstprocessing period; calculating a first concentration of a lightabsorbing substance in blood of the subject based on the first changeamount and the second change amount; and providing a calculated result.17. The method of claim 16, further comprising: obtaining a differentialsignal by differentiating the one of the first signal and the secondsignal; and setting the first processing period in the first periodbased on a minimum value of the differential signal.
 18. The method ofclaim 16, further comprising: obtaining a differential signal bydifferentiating the one of the first signal and the second signal; andsetting the first processing period in the second period based on amaximum value of the differential signal.
 19. The method of claim 16,wherein the one of the first signal and the second signal is the firstsignal, wherein the one of the first period and the second period is thefirst period, wherein the method further comprises: extracting thesignal cycle corresponding to the cardiac cycle of the subject for thesecond signal; setting a second processing period in the second period;obtaining a third change amount corresponding to an attenuation changeamount of the first light in the second processing period based on thefirst signal in the second processing period; obtaining a fourth changeamount corresponding to an attenuation change amount of the second lightin the second processing period based on the second signal in the secondprocessing period; calculating a second concentration corresponding tothe concentration of the light absorbing substance in blood of thesubject in the second processing period based on the third change amountand the fourth change amount; and calculating a transit time of blood inthe biological tissue based on the first concentration and the secondconcentration.
 20. The method of claim 16, further comprising: obtaininga correlation coefficient between the first signal and the secondsignal; and calculating a transit time of blood in the biological tissuebased on time-dependent change of the correlation coefficient.